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EP3131458B1 - Système et logiciel d'amélioration d'imagerie par résonance magnétique à contraste dynamique à phases multiples - Google Patents

Système et logiciel d'amélioration d'imagerie par résonance magnétique à contraste dynamique à phases multiples Download PDF

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Publication number
EP3131458B1
EP3131458B1 EP15718101.7A EP15718101A EP3131458B1 EP 3131458 B1 EP3131458 B1 EP 3131458B1 EP 15718101 A EP15718101 A EP 15718101A EP 3131458 B1 EP3131458 B1 EP 3131458B1
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EP
European Patent Office
Prior art keywords
magnetic resonance
image data
interest
subject
fat
Prior art date
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EP15718101.7A
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German (de)
English (en)
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EP3131458A1 (fr
Inventor
Nadine GDANIEC
Peter Boernert
Mariya Ivanova Doneva
Ivan PEDROSA
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Koninklijke Philips NV
UT Southwestern Medical Center
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Koninklijke Philips NV
UT Southwestern Medical Center
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4869—Determining body composition
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/4828—Resolving the MR signals of different chemical species, e.g. water-fat imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
    • G01R33/56509—Correction of image distortions, e.g. due to magnetic field inhomogeneities due to motion, displacement or flow, e.g. gradient moment nulling
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/0002—Inspection of images, e.g. flaw detection
    • G06T7/0012—Biomedical image inspection
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4869—Determining body composition
    • A61B5/4872—Body fat
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/5601—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution involving use of a contrast agent for contrast manipulation, e.g. a paramagnetic, super-paramagnetic, ferromagnetic or hyperpolarised contrast agent
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/563—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution of moving material, e.g. flow contrast angiography
    • G01R33/56366—Perfusion imaging
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10072—Tomographic images
    • G06T2207/10088—Magnetic resonance imaging [MRI]
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing
    • G06T2207/30096—Tumor; Lesion

Definitions

  • the invention pertains to a method of operating a magnetic resonance imaging system with regard to acquiring multiple-phase dynamic contrast-enhanced magnetic resonance images, and a magnetic resonance imaging system being operated by employing such a method.
  • DCE dynamic contrast-enhanced
  • Motion artifacts due to respiratory motion of the subject of interest can degrade image quality. Therefore, data are preferably acquired during a series of breath-holds. An acquisition during multiple breath-holds of the subject of interest might result in spatial displacement of the images, because the previous state of motion is not exactly achieved, and also because the patient might be in stress after the contrast agent has been administered.
  • a MRI system including using the the distribution of fat for retrospective motion correction during reconstruction is known from EP2626718 A1 .
  • the object is achieved by configured for acquiring magnetic resonance images of at least a portion of a subject of interest (20), comprising:
  • dynamic magnetic resonance imaging shall be understood particularly as acquiring a magnetic resonance signal with two or three spatial coordinates and time as an additional dimension.
  • dynamic magnetic resonance images may have a sparse representation.
  • water/fat magnetic resonance signal separation technique shall be understood particularly to encompass methods known in the art of clinical magnetic resonance imaging for discriminating and separating the fat signal portion and the water signal portion in acquired magnetic resonance images.
  • image registration shall be understood particularly as a technique of transforming two different sets of image data into one coordinate system.
  • Image registration techniques are commonly known in medical imaging and are commercially available (e.g. MATLAB® module by MathWorks®). The registration transformation is usually determined by optimizing a similarity measure calculated from the different sets of image data.
  • image registration method shall encompass intensity-based and/or feature-based methods, rigid and/or non-rigid image registration as well as local correlation methods and/or registration techniques based on mutual information. Other image registration techniques that appear suitable to the person skilled in the art may as well be applied.
  • the invention is based on the concept that the spatial distribution of fat as determined from the first set of magnetic resonance image data and the spatial distribution of fat as determined from at least the second set of magnetic resonance image data are congruent and can be brought to alignment with high precision by applying an image registration method, as the magnetic resonance signal corresponding to the fat in the portion of the subject of interest is unaffected by the administering of the contrast agent.
  • An advantage of the invention lies in that any motion of the subject of interest occurring between a point in time of acquiring the first set of magnetic resonance image data and a point in time of acquiring at least the second set of magnetic resonance image data can be precisely corrected for despite the fact that the magnetic resonance image has changed because of the administering of the contrast agent.
  • the sets of magnetic resonance image data are acquired during breath-hold periods in the respiration of the subject of interest. In principle, however, they may also be acquired while the subject of interest is breathing in a regular breathing pattern.
  • the method further comprises a step of using the determined first image of the unaltered spatial distribution of fat as prior knowledge for image reconstruction of each set of magnetic resonance image data acquired after administering the contrast agent.
  • the method comprises steps of
  • the water/fat magnetic resonance signal separation technique is based on the difference in the Larmor frequencies of excited nuclei due to chemical shift.
  • the chemical shift is the difference of the resonance frequencies of 3.5 ppm of protons bound in water versus protons bound in fat.
  • the water/fat magnetic resonance signal separation technique is based on the Dixon method, which is known in the art and is first described in the article by Dixon, W. T., "Simple Proton Spectroscopic Imaging", Radiology 153:189 (1984 ).
  • Some embodiments of the Dixon method require acquiring more than one set of magnetic resonance image data, for instance an "in-phase” image set and an “opposed-phased” image set (the terms “in-phase” and “oppose-phased” describing the relation between the spin phases of protons bound in water and protons bound in fat), from which separate fat and water images can be calculated.
  • image data required for one water/fat magnetic resonance signal separation approach are considered as acquiring one set of magnetic resonance image data. In this way, images of the spatial distribution of fat of at least the portion of the subject of interest can readily be obtained.
  • the method further comprises steps of
  • the determined spatial distribution of the local static magnetic field strength can be utilized for correlating spin phase disturbances induced by variations of the static magnetic field strength that comply with the acquired magnetic resonance data. These correlations can advantageously be used for improving and/or expediting the image reconstruction process.
  • At least one of the second set of magnetic resonance image data or at least one set of magnetic resonance image data of the plurality of sets of magnetic resonance image data acquired after administering the contrast agent is obtained by employing a compressed sensing method.
  • compressed sensing is known as a method of image reconstruction that provides a potentially significant reduction of acquisition time.
  • Examples of compressed sensing magnetic resonance imaging are, for instance, given in the article by M. Lustig et al., "Sparse MRI: The Application of Compressed Sensing for Rapid MR Imaging", Magnetic Resonance in Medicine 58:1182-1195 (2007 ).
  • the method comprises a step of applying a filter to a set of magnetic resonance image data acquired prior to administering the contrast agent to the subject of interest, wherein the filter is equivalent to a high pass filter in k-space.
  • a filter is equivalent to a high pass filter in k-space.
  • the magnetic resonance imaging system is provided that is configured for acquiring magnetic resonance images of at least a portion of a subject of interest.
  • the magnetic resonance imaging system comprises
  • the control unit is configured to carry out steps of an embodiment of the methods disclosed herein or a combination thereof.
  • a software module for carrying out an embodiment of any of the methods disclosed above or a combination thereof, of operating a magnetic resonance imaging system with regard to acquiring multiple-phase dynamic contrast-enhanced magnetic resonance images.
  • the method steps to be conducted are converted into a program code of the software module, wherein the program code is implementable in a memory unit of the magnetic resonance imaging system and is executable by a processor unit of the magnetic resonance imaging system.
  • the processor unit may be the processor unit of the control unit that is customary for controlling functions of a magnetic resonance imaging system.
  • the processor unit may, alternatively or supplementary, be another processor unit that is especially assigned to execute at least some of the method steps.
  • the software module can enable a robust and reliable execution of the method and can allow for a fast modification of method steps.
  • Fig. 1 shows a schematic illustration of a part of an embodiment of a magnetic resonance imaging system 10 configured for acquiring magnetic resonance images of at least a portion of a subject of interest 20, usually a patient.
  • the magnetic resonance imaging system 10 comprises a scanning unit 12 having a main magnet 14.
  • the main magnet 14 has a central bore that provides an examination space 16 around a center axis 18 for the subject of interest 20 to be positioned within, and is further provided for generating a static magnetic field Bo at least in the examination space 16.
  • a customary table for supporting the subject of interest 20 has been omitted in Fig. 1 .
  • the static magnetic field Bo defines an axial direction of the examination space 16, aligned in parallel to the center axis 18. It is appreciated that the invention is also applicable to any other type of magnetic resonance imaging systems providing an examination region within a static magnetic field.
  • the magnetic resonance imaging system 10 comprises a magnetic gradient coil system 22 provided for generating gradient magnetic fields superimposed to the static magnetic field Bo.
  • the magnetic gradient coil system 22 is concentrically arranged within the bore of the main magnet 14.
  • the magnetic resonance imaging system 10 comprises a control unit 26 configured to control functions of the magnetic resonance imaging system 10.
  • the control unit 26 includes a human interface device 24 including a monitor unit having a touch-sensitive screen.
  • the magnetic resonance imaging system 10 includes a radio frequency antenna device 36 designed as a whole-body coil that is provided for applying a radio frequency excitation field B 1 to nuclei of or within the subject of interest 20 for magnetic resonance excitation during radio frequency transmit time periods to excite the nuclei of or within the subject of interest 20 for the purpose of magnetic resonance imaging.
  • radio frequency power is fed, controlled by the control unit 26, from a radio frequency transmitter 40 to the whole-body coil.
  • the whole-body coil has a center axis and, in the operational state, is arranged concentrically within the bore of the main magnet 14 such that the center axis of the whole-body coil and the center axis 18 of the scanning unit 12 coincide.
  • a cylindrical metal radio frequency shield 34 is arranged concentrically between the magnetic gradient coil system 22 and the whole-body coil.
  • the magnetic resonance imaging system 10 comprises a plurality of radio frequency antenna devices 38 provided for receiving magnetic resonance signals from the nuclei of or within the subject of interest 20 that have been excited by applying the radio frequency excitation field B 1 .
  • the radio frequency antenna devices 38 of the plurality of radio frequency antenna devices 38 are designed as an array of local coils that are intended to be positioned proximal to a region of the subject of interest 20 to be imaged, namely the liver.
  • the local coils are configured for receiving magnetic resonance signals from the excited nuclei of or within the portion of the subject of interest 20 to be imaged during radio frequency receiving time periods which are distinct from the radio frequency transmit time periods.
  • the magnetic resonance imaging system 10 comprises an image processing unit 32 provided for processing magnetic resonance signals to determine magnetic resonance images of at least the portion of the subject of interest 20 from the received magnetic resonance signals.
  • the magnetic resonance imaging system 10 further comprises a respiration monitoring device 42.
  • the respiration monitoring device 42 includes a respiration sensor that, in an operational state, is attached to the thorax of the subject of interest 20 and is held by a belt which is wound around the thorax. It is appreciated by the one skilled in the art that other types of respiration monitoring devices are as well employable.
  • the respiration monitoring device 42 is configured to provide the control unit 26 with an output signal whose level represents a respiration state of the subject of interest 20. To this end, an output line of the respiration monitoring device 42 is connected to the control unit 26.
  • the control unit 26 of the magnetic resonance imaging system 10 is configured for receiving an output signal from the respiration monitoring device 42.
  • the output signal is displayed on the monitor unit of the human interface device 24. In this way, a breathing pattern and, in particular, breath-hold periods can be checked by an operator.
  • Magnetic resonance image acquisition during individual breath-holds is performed using a breath-hold adaptive sampling pattern.
  • a related fast sampling scheme could be employed.
  • the spatial resolution of the magnetic resonance image is automatically adapted during image acquisition, and is combined with the output signal of the respiration monitoring device 42 in such a way that the acquisition of the magnetic resonance image is terminated at breathing onset. Premature onset of breathing results in an incomplete set of magnetic resonance image data.
  • the adaptive sampling pattern is designed to ensure incoherence at every instance in time, which enables to apply a compressed sensing reconstruction method.
  • control unit 26 comprises a software module 44 ( Fig. 1 ).
  • the method steps to be conducted are converted into a program code of the software module 44, wherein the program code is implementable in a memory unit 28 of the control unit 26 and is executable by a processor unit 30 of the control unit 26.
  • a preparatory step 46 via the touch-sensitive screen of the human interface device 24, the operator selects a transversal plane of the portion of the subject of interest 20 to be imaged and the number of phases to be imaged from the portion of the subject of interest 20 before and after administering a contrast agent.
  • threshold signal levels of the output signal of the respiration monitoring device 42 which correspond to a respiration breath-hold at full inspiration of the subject of interest 20 have been determined.
  • a minimum value of the threshold signal level is stored in the memory unit 28 of the control unit 26.
  • a first set of magnetic resonance image data x pre is acquired during a breath-hold period in the respiration of the subject of interest 20 at two different echo times.
  • a first image of the spatial distribution of fat I pre of at least the portion of the subject of interest 20 is determined in another step 50 from a full image reconstruction, by employing a water/fat magnetic resonance signal separation technique that is based on the Dixon method, wherein magnetic resonance image data are acquired at one echo time or more than one different echo times.
  • the first set of magnetic resonance image data x pre is acquired at two different echo times.
  • the Dixon method well known in the art, is based on the difference in the Larmor frequencies of excited nuclei, in this embodiment given by protons, due to chemical shift.
  • a gadolinium-based contrast agent is administered to the subject of interest 20 as an intravenous bolus injection.
  • a second set of magnetic resonance image data x 2 of at least the portion of the subject of interest 20 is acquired in the arterial phase and during another breath-hold period in the respiration of the subject of interest 20, wherein the second set of magnetic resonance image data x2 is acquired at two (alternatively three) different echo times.
  • a second image of the spatial distribution of fat I 2 ph of at least the portion of the subject of interest 20 is determined in another step 54 from an iterative image reconstruction using the water/fat magnetic resonance signal separation technique based on the Dixon method, as will be described later on.
  • the magnetic resonance image signal stemming from the excited protons bound in the fat tissue of at least a portion of the subject of interest 20 is not affected by the administered contrast agent. Therefore, the image of the spatial distribution of fat I pre obtained from the first set of magnetic resonance image data x pre and the image of the spatial distribution of fat I 2 ph obtained from the second set of magnetic resonance image data x 2 are substantially congruent, and a transformation function D ph 21 exists that minimizes a difference between the first image of the spatial distribution of fat I pre and the second image of the spatial distribution of fat I 2 ph . The difference is understood with regard to a suitable, specified mathematical norm.
  • the control unit 26 of the magnetic resonance imaging system 10 includes a rigid-type image registration using software residing in the memory unit 28 of the control unit 26 and being executable by the processor unit 30 of the control unit 26.
  • the determined transformation D 21 ph is applied to the acquired second set of magnetic resonance image data x 2 for correcting a potential motion of the subject of interest 20 having occurred in the time between acquiring the first set of magnetic resonance image data x pre and the second set of magnetic resonance image data x 2 .
  • the determined first image of the spatial distribution of fat I pre is used as prior knowledge for applying image reconstruction to the second set of magnetic resonance image data x 2 which has been acquired after administering the contrast agent.
  • the second set of magnetic resonance image data x 2 is thereby obtained by employing parallel imaging or a compressed sensing method for image reconstruction, wherein prior knowledge is given by the existing determined first image of the spatial distribution of fat I pre , which allows for potential higher under-sampling for the magnetic resonance images to be acquired after administering the contrast agent.
  • a third set of magnetic resonance image data x 3 is acquired in the portal venous phase and during another breath-hold period in the respiration of the subject of interest 20, wherein magnetic resonance data are acquired at two (alternatively three) different echo times.
  • the third set of magnetic resonance image data x 3 is obtained by employing parallel imaging or the method of compressed sensing for image reconstruction, wherein the already existing starting basis, given by the determined first image of the spatial distribution of fat I pre , again allows applying the under-sampling method as described before.
  • a third image of the spatial distribution of fat I 3 ph of at least the portion of the subject of interest 20 is determined using the water/fat magnetic resonance signal separation technique based on the Dixon method.
  • the determined transformation D 31 ph is applied to the acquired third set of magnetic resonance image data x 3 for correcting a potential motion of the subject of interest 20 having occurred in the time between acquiring the second magnetic resonance image x 2 and the third magnetic resonance image x 3 .
  • a fourth set and a fifth set of magnetic resonance image data x 4 , x 5 of at least the portion of the subject of interest 20 are acquired in the delayed venous phase and in the phase of equilibrium, respectively, during other breath-hold periods in the respiration of the subject of interest 20, wherein the magnetic resonance data are acquired at two (alternatively three) different echo times.
  • the fourth and the fifth set of magnetic resonance image data x 4 , x 5 are obtained by employing the method of compressed sensing for image reconstruction, with the determined first image of the spatial distribution of fat I pre as starting basis, and by applying the under-sampling method as described above.
  • a fourth image of the spatial distribution of fat I 4 ph and a fifth image of the spatial distribution of fat I 5 ph of at least the portion of the subject of interest 20 are determined using the water/fat magnetic resonance signal separation technique based on the Dixon method.
  • Transformations D 41 ph and D 51 ph are determined by applying the image registration method to the fourth image of the spatial distribution of fat I 4 ph and the fifth image of the spatial distribution of fat I 5 ph , respectively, with reference to the first image of the spatial distribution of fat I pre , via the control unit.
  • the second to fifth set of magnetic resonance image data x 2 to x 5 acquired after administering the contrast agent to the subject of interest 20 are commonly obtained by employing a compressed sensing method for image reconstruction, wherein
  • the first term enforces sparsity of the acquired image in an adequate transform domain.
  • the second term of the expression ensures data consistency at locations in k-space that were acquired.
  • the third term of the expression considers the potential motion of the subject of interest 20, occurring between a point in time of acquiring the first set of magnetic resonance image data x pre and a point in time of acquiring the i-th set of magnetic resonance image data x i .
  • the fourth term of the expression reflects similarity of high frequencies in an applicable domain, which is preferably represented by the k-space, from data acquired prior to administering the contrast agent and after administering the contrast agent.
  • the regularization parameters ⁇ 1 , ⁇ 2 , ⁇ 3 can be inputted by the operator via the human interface device 24 as weighting factors. At least one of the regularization parameters ⁇ 1 , ⁇ 2 , ⁇ 3 can be chosen as zero.

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Claims (10)

  1. Système d'imagerie par résonance magnétique (10) configuré pour acquérir des images par résonance magnétique d'au moins une partie d'un sujet d'intérêt (20), comprenant :
    - un espace d'examen (16) prévu pour positionner au moins la partie du sujet d'intérêt (20) à l'intérieur ;
    - un aimant principal (14) configuré pour générer un champ magnétique statique Bo dans l'espace d'examen (16) ;
    - un système de bobine de gradient magnétique (22) configuré pour générer des champs magnétiques à gradients superposés au champ magnétique statique B0 ;
    - au moins un dispositif d'antenne radiofréquence (36) qui est configuré pour appliquer un champ d'excitation radiofréquence B1 aux noyaux du sujet d'intérêt (20) ou à l'intérieur de la partie de celui-ci pour excitation par résonance magnétique ;
    - au moins un dispositif d'antenne radiofréquence (38) qui est configuré pour recevoir des signaux de résonance magnétique des noyaux du sujet d'intérêt (20) ou à l'intérieur de la partie de celui-ci, qui ont été excités en appliquant le champ d'excitation radiofréquence B1 ;
    - une unité de commande (26) configurée pour commander des fonctions du système d'imagerie par résonance magnétique (10) ;
    - une unité de traitement d'image (32) configurée pour traiter des signaux de résonance magnétique pour déterminer des images par résonance magnétique d'au moins la partie du sujet d'intérêt (20) à partir des signaux de résonance magnétique reçus ;
    dans lequel l'unité de commande (26) est configurée pour réaliser un procédé d'acquisition d'images dynamiques par résonance magnétique à contraste amélioré à phases multiples, dans lequel une image par résonance magnétique ou plusieurs images sont acquises avant administration de l'agent de contraste, et dans lequel des images multiples sont acquises au niveau d'un nombre spécifié de phases après administration de l'agent de contraste, le procédé comprenant les étapes suivantes :
    - acquisition (48) d'au moins un premier ensemble de données d'images par résonance magnétique (xpre) avant administration d'un agent de contraste au sujet d'intérêt (20),
    - en utilisant une technique de séparation de signal de résonance magnétique eau/graisse, détermination (52) d'une première image d'une distribution spatiale de graisse (Ipre) d'au moins la partie du sujet d'intérêt (20) à partir du premier ensemble de données d'image par résonance magnétique (Xpre),
    - acquisition (50) d'une pluralité d'ensembles de données d'image par résonance magnétique (xi) d'au moins la partie du sujet d'intérêt (20) après administration de l'agent de contraste au sujet d'intérêt (20),
    - en utilisant une technique de séparation de signal de résonance magnétique eau/graisse, détermination (54) d'au moins une seconde image de la distribution spatiale de graisse (I2 ph) d'au moins la partie du sujet d'intérêt (20) à partir du second ensemble de données d'image par résonance magnétique (x2),
    - application (56) d'un procédé d'enregistrement d'image à au moins la seconde image de la distribution spatiale de graisse (I2 ph) en référence à la première image de la distribution spatiale de graisse (Ipre) pour corriger un mouvement potentiel du sujet d'intérêt (20) s'étant produit au moment entre l'acquisition du premier ensemble de données d'image par résonance magnétique (xpre) et l'acquisition d'au moins le second ensemble de données d'image par résonance magnétique (x2)
    - utilisation (60) de la première image déterminée de la distribution spatiale de graisse (Ipre) en tant que connaissance préalable pour la reconstruction d'image de chaque ensemble de données d'image par résonance magnétique de la pluralité d'ensembles de données d'image par résonance magnétique (xi) acquis après administration de l'agent de contraste.
  2. Système d'imagerie par résonance magnétique selon l'une quelconque des revendications précédentes, dans lequel la technique de séparation de signal de résonance magnétique eau/graisse est basée sur la différence des fréquences de Larmor des noyaux excités due au déplacement chimique.
  3. Système d'imagerie par résonance magnétique selon l'une quelconque des revendications précédentes, dans lequel l'unité de commande est configurée en outre pour réaliser un procédé comprenant les étapes suivantes :
    - obtention, à partir de la détermination de la première image de la distribution spatiale de graisse (Ipre) d'au moins la partie du sujet d'intérêt (20) à partir du premier ensemble de données d'image par résonance magnétique (xpre), d'une distribution spatiale d'une intensité de champ magnétique statique local B0,
    - reconstruction d'images de résonance magnétique à partir de l'un quelconque des ensembles de données d'image par résonance magnétique (xi) après administration de l'agent de contraste au sujet d'intérêt (20) en utilisant la distribution spatiale obtenue de l'intensité du champ magnétique statique local B0.
  4. Système d'imagerie par résonance magnétique selon l'une quelconque des revendications précédentes, dans lequel au moins l'un du second ensemble de données d'image par résonance magnétique (x2) ou au moins un ensemble de données d'image par résonance magnétique de la pluralité d'ensembles de données d'image par résonance magnétique (xi) acquis après administration de l'agent de contraste est obtenu par utilisation d'un procédé d'acquisition comprimée.
  5. Système d'imagerie par résonance magnétique selon l'une quelconque des revendications précédentes, dans lequel l'unité de commande est configurée en outre pour réaliser un procédé comprenant l'étape suivante :
    - application d'un filtre aux données d'image par résonance magnétique acquises avant administration de l'agent de contraste au sujet d'intérêt (20), dans lequel le filtre est équivalent à un filtre passe-haut dans l'espace k.
  6. Module logiciel (44) pour réaliser les opérations d'un système d'imagerie par résonance magnétique (10) relatives à l'acquisition d'images par résonance magnétique à contraste amélioré dynamique à phases multiples, dans lequel une image par résonance magnétique ou plusieurs images sont acquises avant administration de l'agent de contraste, et dans lequel de multiples images sont acquises au niveau d'un nombre spécifié de phases après administration de l'agent de contraste, dans lequel le procédé (48-60) devant être opéré est converti en un code de programme du module logiciel (44), dans lequel le code de programme peut être mis en œuvre dans une unité de mémoire (28) du système d'imagerie par résonance magnétique (10) et exécuté par une unité de processeur (30) du système d'imagerie par résonance magnétique (10), dans lequel le procédé comprend les étapes suivantes :
    - acquisition (48) d'au moins un premier ensemble de données d'images par résonance magnétique (xpre) avant administration d'un agent de contraste au sujet d'intérêt (20),
    - en utilisant une technique de séparation de signal de résonance magnétique eau/graisse, détermination (52) d'une première image d'une distribution spatiale de graisse (Ipre) d'au moins la partie du sujet d'intérêt (20) à partir du premier ensemble de données d'image par résonance magnétique (xpre),
    - acquisition (50) d'une pluralité d'ensembles de données d'image par résonance magnétique (xi) d'au moins la partie du sujet d'intérêt (20) après administration de l'agent de contraste au sujet d'intérêt (20),
    - en utilisant une technique de séparation de signal de résonance magnétique eau/graisse, détermination (54) d'au moins une seconde image de la distribution spatiale de graisse (I2 ph) d'au moins la partie du sujet d'intérêt (20) à partir du second ensemble de données d'image par résonance magnétique (x2),
    - application (56) d'un procédé d'enregistrement d'image à au moins la seconde image de la distribution spatiale de graisse (I2 ph) en référence à la première image de la distribution spatiale de graisse (Ipre) pour corriger un mouvement potentiel du sujet d'intérêt (20) s'étant produit au moment entre l'acquisition du premier ensemble de données d'image par résonance magnétique (xpre) et l'acquisition d'au moins le second ensemble de de données d'image par résonance magnétique (x2)
    - utilisation (60) de la première image déterminée de la distribution spatiale de graisse (Ipre) en tant que connaissance préalable pour la reconstruction d'image de chaque ensemble de données d'image par résonance magnétique de la pluralité d'ensembles de données d'image par résonance magnétique (xi) acquis après administration de l'agent de contraste.
  7. Module logiciel selon la revendication 6 précédente, dans lequel la technique de séparation de signal de résonance magnétique eau/graisse est basée sur la différence des fréquences de Larmor des noyaux excités due au déplacement chimique.
  8. Module logiciel selon l'une quelconque des revendications 6 ou 7 précédentes, dans lequel le procédé comprend en outre les étapes suivantes :
    - obtention, à partir de la détermination de la première image de la distribution spatiale de graisse (Ipre) d'au moins la partie du sujet d'intérêt (20) du premier ensemble de données d'image par résonance magnétique (xpre), d'une distribution spatiale d'une intensité de champ magnétique statique local B0,
    - reconstruction d'images de résonance magnétique à partir de l'un quelconque des ensembles de données d'image par résonance magnétique (xi) après administration de l'agent de contraste au sujet d'intérêt (20) en utilisant la distribution spatiale obtenue de l'intensité du champ magnétique statique local Bo.
  9. Module logiciel selon l'une quelconque des revendications 6 à 8 précédentes, dans lequel au moins l'un du second ensemble de données d'image par résonance magnétique (x2) ou au moins un ensemble de données d'image par résonance magnétique de la pluralité d'ensembles de données d'image par résonance magnétique (xi) acquis après administration de l'agent de contraste est obtenu par utilisation d'un procédé d'acquisition comprimée.
  10. Module logiciel selon l'une quelconque des revendications 6 à 9 précédentes, dans lequel le procédé comprend en outre l'étape suivante :
    - application d'un filtre aux données d'image par résonance magnétique acquises avant administration de l'agent de contraste au sujet d'intérêt (20), dans lequel le filtre est équivalent à un filtre passe-haut dans l'espace k.
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